Ultrasound system for enhanced instrument visualization

ABSTRACT

An ultrasound imaging system includes a processor programmed to generate an anatomy image and a number of needle frames at different transmit beam angles. The system analyzes the data in the needle frames and selects segments therein that are identified as likely representing an interventional instrument. Data from one or more needle frames are blended with the data for the anatomy image of the tissue to create a composite image of the tissue and the interventional instrument.

This application is a continuation of co-pending U.S. application Ser.No. 15/347,697 filed Nov. 9, 2016, which is incorporated herein byreference.

TECHNICAL FIELD

The disclosed technology relates to ultrasound imaging systems and inparticular to ultrasound imaging systems for imaging interventionalinstruments within a body.

BACKGROUND

Ultrasound imaging is becoming increasingly accepted as the standard ofcare to be used when guiding an interventional instrument to a desiredlocation within a body. One common use for this procedure is during theapplication of anesthesia, whereby a physician or a medical technicianviews an ultrasound image to help guide a needle to a desired nerve or aregion of interest. To enhance the ability of the physician to view theneedle, many ultrasound systems incorporate so called “needlevisualization” technologies that produce a composite image from ananatomy image of the tissue and an image of the needle.

One of the common problems associated with most needle visualizationtechniques is that the beam direction of the ultrasound system used toimage the needle has to be preset by the user. In order to obtain thebest image, the transmit beam direction should be nearly perpendicularto a needle or other interventional instrument. If the needle does notappear clearly in the composite image of the tissue, then the user issupposed to change the settings on the machine to vary the beamdirection. This is often too cumbersome for an unassisted operator whenthe operator has one hand holding the ultrasound probe and another handguiding the needle. Even if the operator has an assistant, it is oftendistracting to instruct the assistant to change the beam directionsettings, which may need frequent adjustment depending on how the probeis held and how the instrument is advanced into the body. Therefore,many procedures are performed where the transmit beam direction forvisualizing a needle or other interventional instrument is not set inthe optimal direction.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a simplified illustration of an ultrasound imaging system forproducing and displaying a composite image of tissue and aninterventional instrument in accordance with one embodiment of thedisclosed technology;

FIG. 2 is a block diagram of an ultrasound imaging system in accordancewith an embodiment of the disclosed technology; and

FIGS. 3A-3C show representative composite frames obtained by combiningimage data with echo data representing an interventional instrument fromsingle needle frame transmissions at shallow, medium and steep transmitangles, respectively;

FIG. 3D illustrates a representative composite image created by blendingecho data from one or more of the needle frames shown in FIGS. 3A-3Cwith echo data for an anatomy image in accordance with an embodiment ofthe disclosed technology; and

FIG. 4 shows a number of needle frames whereby one or more of the framerate, line density or multi-line processing are adjusted for framesobtained with transmit beam angles that are not nearly perpendicular tothe orientation of an interventional instrument in accordance with anembodiment of the disclosed technology.

DETAILED DESCRIPTION

As will be explained in further detail below, the disclosed technologyrelates to improvements in ultrasound imaging systems and in particularto an ultrasound imaging system that is configured to produce a combinedimage of tissue and an instrument that is inserted into the tissue. Inthe description below, the interventional instrument is described asbeing a needle used to deliver anesthesia or other drugs to a desiredlocation. However, other devices such as biopsy needles, needles forsuturing tissue, needles for withdrawing fluids (e.g. amniocentesis),robotic surgical instruments, catheters, guidewires or other invasivemedical instruments can also be imaged.

In one embodiment, a processor in the ultrasound system is configured tocause a number of transmit beams to be created and delivered to a bodyin order to produce an anatomy image of the tissue under examination. Inaddition, the processor is configured to cause a number of transmitbeams to be generated at different transmit beam angles in order toimage an interventional instrument. To distinguish the anatomy imagefrom the images of the interventional instrument, the frames of theinterventional instrument can be referred to as “needle frames,” even ifthe instrument is not a needle.

Each of the needle frames produced from the transmissions at thedifferent transmit angles is analyzed to detect the presence of aninterventional instrument. In one embodiment, a composite image iscreated using the anatomy image and echo data from one or more of theneedle frames that are captured using the different transmit beamdirections in order to show both the tissue and the position of theinterventional instrument.

FIG. 1 shows a representative ultrasound imaging system that implementsthe disclosed technology for imaging the tissue of a patient. In oneembodiment, an ultrasound imaging system 10 can be a hand-held, portableor cart-based system that uses a transducer probe 12 to transmitultrasound signals into a region of interest and to receive thecorresponding echo signals in order to produce an image of the tissuebeing scanned. The probe 12 can be a one or two dimensional linear orcurved transducer or a phased array transducer all of which canselectively change the transmit beam angles electronically.

The ultrasound imaging system 10 converts characteristics of thereceived echo signals (e.g. their amplitude, phase, power, frequencyshift etc.) into data that is quantified and displayed for the user asan image. The images created may also be stored electronically fordigital record keeping or transmitted via a wired or wirelesscommunication link to another device or location. In some embodiments,an operator guides an interventional instrument 15 into the patient (orsubject) 20 with one hand while holding the probe 12 with the otherhand. The operator views a composite image 22 of the tissue and arepresentation 24 of where the interventional instrument is located inthe tissue. The composite image 22 is updated on the screen while theinstrument is guided to the target location. Such a location may be aparticular nerve site in the field of anesthesia or other area ofinterest such as a vessel or a particular organ (e.g. uterus, prostate,tumor, heart vessel etc.).

As will be understood by those skilled in the art, the optimal beamdirection for imaging a long thin interventional instrument is at anangle that is approximately perpendicular to the length of theinstrument. However, the imaging parameters and beam directions requiredto image an instrument are often not the same as those that are optimalfor imaging the tissue. In one embodiment of the disclosed technology,the user is not required to select a particular beam angle to use ingenerating the needle frames. Instead, the processor is programmed togenerate needle frames using multiple different transmit beam angles.The echo data for the needle frames created from these differenttransmit beam angles are analyzed to detect the presence of objects thatmay be an interventional instrument. Echo data from one or more of theneedle frames obtained using different transmit beam directions and thatlikely represent an interventional instrument are copied from the needleframes and blended with the echo data for the anatomy image in order toproduce the composite image that shows both the tissue and the positionof the interventional instrument.

FIG. 2 shows a simplified block diagram of an ultrasound imaging systemin accordance with an embodiment of the disclosed technology. As will beappreciated by those skilled in the art, the ultrasound system may beconstructed with components that are different than those shown. Inaddition, the ultrasound system includes parts that are not discussed(e.g. a power supply etc.) and that are not necessary for theunderstanding of how to make and use the disclosed technology. In theembodiment shown, the ultrasound system includes a processor 40 having abuilt-in or external memory (not shown) containing instructions that areexecutable by the processor to operate the ultrasound imaging system aswill be explained in detail below. In the transmit path, the ultrasoundsystem includes a transmit beamformer 42, a transmit gain controlamplifier 44 and a transmit/receive switch 46. If the ultrasound probe12, is a phased array type or can otherwise change the angle oftransmissions electronically, the transmit beamformer 42 operates togenerate a number of signals having a relative amplitude and phase(timing) that are selected to produce an ultrasound beam from some orall of the transducer elements of the probe that constructively add in adesired transmit beam direction (the desired transmit beam angle). Thesignals from the transmit beamformer are amplified by the transmitamplifier 44 to a sufficiently high voltage level that will cause thetransducer elements to produce the desired acoustic signals in thetissue being examined. In some embodiments, the processor 40 isconnected to supply a control command such as a digital value (e.g.0-255) to the gain control amplifier. The value of the command controlsthe amount of gain that is supplied by the transmit amplifier 44.

Other techniques for adjusting the power of the ultrasound signalsinclude changing the waveforms that drive the transducer elements toeither increase or decrease the power of the ultrasound signals. Inanother embodiment, the voltage rails (+V, −V) of an amplifier thatproduces the driving signals can be changed in order to vary the powerof the ultrasound signals. In yet another embodiment, driving signalscan be supplied to a lessor or a greater number of transducer elementsto change the power of the ultrasound signals. Those skilled in art willunderstand that these techniques are merely exemplary and that there arenumerous ways in which the level of acoustic power of the ultrasoundsignals delivered to the patient can be adjusted.

The amplified transmit signals are supplied to the transducer probe 12through the transmit/receive switch 46, which disconnects or shieldssensitive receive electronics from the transmit signals at the time theyare delivered to the transducer probe 12. After the signals aretransmitted, the transmit/receive switch 46 connects the receiveelectronics to the transducer elements to detect the correspondingelectronic echo signals created when the returning acoustic wavesimpinge upon the transducer elements.

In the receive path, the ultrasound imaging system includes a low noiseamplifier 50, a time gain control (TGC) amplifier 52, an analog todigital converter 54, a receive beamformer 56 and an image processor 58.Analog echo signals produced by the imaging probe are directed throughthe transmit/receive switch 46 to the low noise amplifier where they areamplified. The TGC amplifier 52 applies a variable amplification to thereceived signals that varies the level of amplification applied with thereturn time of the signals (e.g. proportional to the depth in the tissuebeing imaged) to counteract the attenuation of the signals versus depth.The amplified signals are then converted into a digital format by theanalog to digital converter 54. The digitized echo signals are thendelayed and summed by the receive beamformer 56 before being supplied tothe image processor.

In some embodiments, the number of transmitted beams and received beams(lines) may differ from each other. For example, the receive beamformermay produce in parallel (i.e., simultaneously) two or more adjacentlines per transmitted beam, a technique sometimes known as parallelreceive beamforming or multi-line processing. Multi-line processing maybe used to increase the imaging frame rate by lowering the number oftransmitted beams while still being able to keep the number of receivedlines per frame (line density) constant. Alternatively, a highermulti-line order (number of receive lines beamformed in parallel from asingle transmitted beam) may be used to increase the number of receivedlines per frame while keeping the number of transmitted beams, hence theframe rate, constant. Other combinations of line density, frame rate andmulti-line order are also possible. Furthermore, it is even possible totransmit an unfocused beam (plane wave) and beamform all the receivelines of a frame from that single transmitted beam. The system may alsoemploy different combinations of line density and multi-line order forimaging the tissue vs. imaging an interventional instrument. However, itwill be appreciated by those skilled in the art that use of a highermulti-line order, a lower-line density, or unfocused transmit beams,while improving the frame rate, may reduce the quality of the acquiredimages.

Images produced by the image processor 58 from the received signals aredisplayed on a display 60. In addition, the images can be recorded in animage memory (not shown) for future recall and review. A number ofinputs 72 are provided to allow an operator to change various operatingparameters of the ultrasound imaging system and to enter data such asthe patient's name or other record keeping data. In addition, theultrasound imaging system includes input/output (1/0) circuitry to allowthe system to connect to computer communication links (LAN, WAN,Internet etc.) through a wired (e.g. Ethernet, USB, Thunderbolt,Firewire, or the like) or wireless (802.11, cellular, satellite,Bluetooth or the like) communication link.

The details of the components that comprise the ultrasound imagingsystem and how they operate are generally considered to be well known tothose of ordinary skill in the art. Although the ultrasound imagingsystem is shown having many separate components, it will be appreciatedthat devices such as ASICs, FPGAs, digital signal processors (DSPs),CPUs or GPUs may be used to perform the function of multiple ones ofthese individual components.

As discussed above, the processor 40 is programmed to create a compositeimage of the tissue being examined and an interventional instrumentbeing introduced into the tissue. In one embodiment, the image processorproduces an anatomy image of the tissue being examined with imagingparameters that are selected for the depth and particular type of tissuebeing scanned. The anatomy image created by the image processor 58 isstored in memory to be combined with echo data for one or more of theneedle frames that are created to locate an interventional instrument.

In one embodiment, the processor causes the transmit electronics toproduce transmit beams in a number of different transmit directions toimage the interventional instrument. For example, the processor 40 maydirect transmit beams to be produced at a shallow, medium and steepangle as measured with respect to a longitudinal axis of the transducerprobe. In most cases, the position of the instrument will show moreclearly in one or more of the needle frames than in the others.

In one embodiment, the echo data for each of the needle frames createdfrom the transmissions at the different transmit angles are analyzed forthe presence of an interventional instrument. Various instrumentdetection algorithms can be used. For example, the images can beanalyzed for the presence of a linear segment of pixels that are muchbrighter (e.g. greater amplitude) than adjacent pixels therebyindicating the presence of a strong linear reflector. The length of thesegments that may represent an interventional instrument may vary and insome embodiments, may be curved if the interventional instrument itselfis curved or bends when the instrument is inserted. Alternatively, thesegments may seem to be curved in the coordinate system where detectionis performed if the images were acquired using a curved transducergeometry (e.g., convex).

In one embodiment, each segment of bright pixels is scored to indicatehow likely the segment represents an interventional instrument. Such ascore can be adjusted by for example, the length of the bright pixelsabove a certain threshold, how straight or linear the segment of pixelsis, how much contrast is present between the bright pixels and theadjacent pixels, how strong the edges around the segment of brightpixels are as determined by a gradient or other edge-detectionoperations, etc. A Hough transform or other similar techniques can beused to determine the location of pixels that lie on a linear orparameterized curved segment, from which a score can also be determined.

In one embodiment, the brightness data values for an image are convertedinto corresponding gradient values by looking at differences betweenadjacent brightness values along the beam lines. A needle or otherbright reflector that is an interventional instrument is generallycharacterized by a large positive gradient (e.g. dark to light) inbrightness values followed closely by a large negative gradient (e.g.light to dark) of brightness values when viewed in the direction fromthe transducer and into the tissue. The gradient values can be filteredto ensure that the large changes in the positive and negative gradientvalues occur within a distance that would be expected for theinterventional instrument. Next, a Hough transform can be used todetermine if the large positive/negative gradient changes occur in alinear pattern in the adjacent beam lines. Scores for the segments oflarge gradient changes can be increased or decreased depending on one ormore of the length of the gradient changes, how close a positivegradient change is from a negative gradient change, how the gradientchanges align spatially from beam to beam.

In one embodiment, segments of echo data are scored according to howlarge the gradients are and how well the gradients align in adjacentbeam lines. Those segments having larger gradients and are more in lineare given greater scores than those with smaller gradients and are lessaligned. A representation of an instrument may comprise a single longsegment or multiple shorter segments and not all segments having thehighest score may originate from the same needle frame.

In one embodiment, echo data representing likely interventionalinstruments from those images with the highest scoring segments arecopied from two or more needle frames and blended with the echo data forthe anatomy image. In another embodiment, echo data are copied from asingle needle frame and blended with the echo data for the anatomyimage.

Other needle visualization techniques for detecting the presence of aneedle or other interventional instrument in an ultrasound image couldalso be used.

In one embodiment, the processor is programmed to identify segments ofpixel data from one or more of the needle frames created from thetransmissions taken at the various transmit angles that have a scorethat indicates the pixels likely represent an interventional instrument.The processor copies the pixel data representing the instrument and usesa blending function to combine the copied pixel data with the pixel datain the anatomy image.

FIGS. 3A-3C show representative composite frames obtained by combiningimage data with echo data representing an interventional instrument fromsingle needle frame transmissions at shallow, medium and steep transmitangles, respectively. In the composite frames shown, it can be seen thatsome needle frames show different parts of the interventional instrumentbetter than others. In one embodiment, the processor copies the pixeldata for various segments obtained using multiple firing angles thathave the highest scores representing an interventional instrument andblends the copied segment pixel data into the anatomy image.

FIG. 3D shows a representative composite image of the tissue that iscreated by blending pixel data copied from one or more of the needleframes obtained at different firing angles and that have a scoreindicating that the data likely represent an interventional instrument.In some embodiments, the data are blended with a feathering function sothat the copied data representing the interventional instrument are seenstrongly in the composite image while the copied data for areassurrounding the instrument blend in lightly with the data for theanatomy image so that the tissue surrounding the instrument can be seen.

FIG. 4 shows a representative region of interest into which a needle isinserted. In the example shown, an anatomy image 100 is obtained with alinear transducer. A number of needle frames are obtained at differingbeam steering angles 110, 112 and 114. An interventional instrument 120is inserted into the image. In the embodiment shown, the differencesbetween the angle of insertion of the instrument and the angles that areperpendicular to the beam angles 110 and 112 are approximately equal.Therefore, the scores of the segments that represent the instrument inthe needle frames created from firings in the beam steering angles 110and 112 should be generally equal. Pixel data from each of these needleframes can therefore be copied and blended into the anatomy image 100.If the insertion angle of the instrument 120 were in a direction thatwas closer to a line perpendicular to the steering angle 114 forexample, then pixel data from the needle frame that was created inresponse to the transmissions at the angle 114 would be copied andblended with the data for the anatomy image.

In the example shown in FIG. 4 , the beam steering angles 110, 112 aredetermined to be the closest to being perpendicular to the insertionangle of the interventional instrument or are otherwise identified asproducing the best image of the instrument based on the scores of thesegments from the echo data received from these transmit angles. In oneembodiment, the frame rate of transmissions at one or more of the angles110 and 112 can be increased because they represent high priorityangles, whereas the frame rate, line density or multi-line processingfor the needle frame created from the beam steering direction 114 can beadjusted because that transmit angle is not a high priority angle as isexplained further below.

In some embodiments, the pixel data used to display the ultrasoundimages are analyzed to detect the presence of an interventionalinstrument. However, it will be appreciated that the echo data that isnot yet converted into pixel data that is ready for display could beanalyzed. For example, echo data that has been amplified, converted todigital and beamformed but not yet scan converted could be analyzed todetect and score segments in the data that represent interventionalinstruments.

As will be appreciated by those skilled in the art, creating a number ofneedle frames at different transmit angles can decrease the frame rateof the ultrasound imaging system. In one embodiment, the processorselects a higher line density and/or a lower multi-line setting for asubset of the needle frames (e.g. high-quality needle frames) than therest of the needle frames (lower-quality needle frames), where thehigh-quality needle frame(s) is/are chosen adaptively based on theorientations of structures detected by the instrument detectionalgorithm with a high score (i.e. a high probability for the presence ofan interventional instrument). If the detection algorithm findsstructures of a similar orientation with high scores in multiple needleframes, the needle frame with an imaging steering angle that wouldinsonate an interventional instrument at a close-to-perpendicular angleto the orientation of the probe can be chosen to be a high qualityneedle frame acquisition and the other needle frames can continue to beacquired as lower quality needle frames. This adaptively pickedhigh-quality needle frame ensures a high quality visualization of the“most-probable” interventional instrument while the remaininglower-quality needle frames would ensure that instruments at otherorientations are not missed and that an operator is not required tomanually select a high-quality needle frame if the angle of theinterventional instrument with respect to the ultrasound scan headchanges during the procedure.

The system may also alter the number and acquisition rate of the needleframes and the angles employed adaptively based on the detection scores.For example, if features with high detection scores are identifiedwithin a needle frame with a certain angle setting, the system maydesignate that angle as a ‘high priority angle” and increase theacquisition rate of needle frames at or close to that angle setting,while dropping the acquisition rate of needle frames at angles fartheraway from the high-priority angle or for needle frames that do notcontain features with high segment scores. In one embodiment, the systemcontinues to acquire and analyze needle frames that have angles fartheraway from the high-priority angle setting as “scouting” needle frames sothat the system can re-asses and change the “high-priority angle” on thefly if features with higher detection scores are detected with thosescouting needle frames at any time. However, the angles of the scoutingneedle frames may be selected to have a larger angle spread between themand/or a lower acquisition rate to minimize the overall impact to theframe rate.

The subject matter and the operations described in this specificationcan be implemented in digital electronic circuitry, or in computersoftware, firmware, or hardware, including the structures disclosed inthis specification and their structural equivalents, or in combinationsof one or more of them. Embodiments of the subject matter described inthis specification can be implemented as one or more computer programs,i.e., one or more modules of computer program instructions, encoded oncomputer storage medium for execution by, or to control the operationof, data processing apparatus.

A computer storage medium can be, or can be included in, acomputer-readable storage device, a computer-readable storage substrate,a random or serial access memory array or device, or a combination ofone or more of them. Moreover, while a computer storage medium is not apropagated signal, a computer storage medium can be a source ordestination of computer program instructions encoded in anartificially-generated propagated signal. The computer storage mediumalso can be, or can be included in, one or more separate physicalcomponents or media (e.g., multiple COs, disks, or other storagedevices).

The term “processor” encompasses all kinds of apparatus, devices, andmachines for processing data, including by way of example a programmableprocessor, a computer, a system on a chip, or multiple ones, orcombinations, of the foregoing. The apparatus can include specialpurpose logic circuitry, e.g., an FPGA (field programmable gate array)or an ASIC (application-specific integrated circuit). The apparatus alsocan include, in addition to hardware, code that creates an executionenvironment for the computer program in question, e.g., code thatconstitutes processor firmware, a protocol stack, a database managementsystem, an operating system, a cross-platform runtime environment, avirtual machine, or a combination of one or more of them. The apparatusand execution environment can realize various different computing modelinfrastructures, such as web services, distributed computing and gridcomputing infrastructures.

A computer program (also known as a program, software, softwareapplication, script, or code) can be written in any form of programminglanguage, including compiled or interpreted languages, declarative orprocedural languages, and it can be deployed in any form, including as astand-alone program or as a module, component, subroutine, object, orother unit suitable for use in a computing environment. A computerprogram may, but need not, correspond to a file in a file system. Aprogram can be stored in a portion of a file that holds other programsor data (e.g., one or more scripts stored in a markup languagedocument), in a single file dedicated to the program in question, or inmultiple coordinated files (e.g., files that store one or more modules,sub-programs, or portions of code). A computer program can be deployedto be executed on one computer or on multiple computers that are locatedat one site or distributed across multiple sites and interconnected by acommunication network.

The processes and logic flows described in this specification can beperformed by one or more programmable processors executing one or morecomputer programs to perform actions by operating on input data andgenerating output. The processes and logic flows can also be performedby, and apparatus can also be implemented as, special purpose logiccircuitry, e.g., an FPGA (field programmable gate array) or an ASIC(application-specific integrated circuit).

Processors suitable for the execution of a computer program include, byway of example, both general and special purpose microprocessors.Devices suitable for storing computer program instructions and datainclude all forms of non-volatile memory, media and memory devices,including by way of example semiconductor memory devices, e.g., EPROM,EEPROM, and flash memory devices; magnetic disks, e.g., internal harddisks or removable disks; magneto-optical disks; and CD-ROM and DVD-ROMdisks. The processor and the memory can be supplemented by, orincorporated in, special purpose logic circuitry.

From the foregoing, it will be appreciated that specific embodiments ofthe invention have been described herein for purposes of illustration,but that various modifications may be made without deviating from thescope of the invention. Accordingly, the invention is not limited exceptas by the appended claims.

I claim:
 1. An ultrasound imaging system comprising: a memory, and oneor more processors coupled to the memory, the one or more processorsconfigured to: acquire tissue echo data for an anatomy image of tissuebeing examined from ultrasound signals; acquire needle echo data forneedle frames associated with the anatomy image that are obtained withtransmit beam angles including a first transmit beam angle and a secondtransmit beam angle with respect to a longitudinal axis of a transducerprobe that receives the ultrasound signals; determine, based on theneedle echo data, segments in the needle frames obtained with the firsttransmit beam angle and the second transmit beam angle; assign scores tothe segments in the needle frames, a first score of the scores assignedto a segment indicating that the segment represents an interventionalinstrument; identify at least one segment of the segments that isassigned the first score; set the first transmit beam angle as apriority angle when the at least one segment that is assigned the firstscore is detected in the needle frames with the first transmit beamangle; acquire one or more first frames of the needle frames with thefirst transmit beam angle at a first line density that is set based onthe priority angle determination; and acquire one or more second framesof the needle frames with the second transmit angle at a second linedensity that is different from the first line density.
 2. The ultrasoundimaging system of claim 1, wherein the at least one segment of thesegments that is assigned the first score is to be blend with the tissueecho data.
 3. The ultrasound imaging system of claim 1, wherein the oneor more processors are configured to: determine that the first transmitbeam angle is nearly perpendicular to an orientation of theinterventional instrument based on the first score.
 4. The ultrasoundimaging system of claim 1, wherein the one or more processors areconfigured to increase the first line density.
 5. The ultrasound imagingsystem of claim 1, wherein the one or more processors are configured todecrease the second line density.
 6. The ultrasound imaging system ofclaim 1, wherein the one or more processors are configured to: set thesecond transmit beam angle as the priority angle when the segment thatrepresents the interventional instrument is detected in the needleframes with the second transmit beam angle; acquire one or more thirdframes of the needle frames with the second transmit beam angle at thefirst line density; and acquire one or more fourth frames of the needleframes with the first transmit angle at the second line density.
 7. Theultrasound imaging system of claim 1, wherein the one or more processorsare configured to increase a frame rate for the acquiring the one ormore first frames.
 8. The ultrasound imaging system of claim 1, whereinthe one or more processors are configured to decrease a number ofreceive lines that are beamformed in parallel for each transmit beam toproduce the one or more first frames.
 9. The ultrasound imaging systemof claim 1, wherein the one or more processors are configured todecrease a frame rate for the acquiring the one or more second frames.10. The ultrasound imaging system of claim 1, wherein the one or moreprocessors are configured to decrease a frame rate of one or more otherframes of the needle frames acquired at angles that are not the firsttransmit beam angle.
 11. The ultrasound imaging system of claim 1,wherein the one or more processors are configured to increase a numberof receive lines that are beamformed in parallel for each transmit beamto produce one or more of the needle frames not at the first transmitbeam angle.
 12. The ultrasound imaging system of claim 1, wherein theone or more processors are configured to blend the segment with thetissue echo data to create a composite image including the anatomy imageof the tissue and the interventional instrument.
 13. An ultrasoundimaging system comprising: a memory, and one or more processors coupledto the memory, the one or more processors configured to: acquire tissueecho data for an anatomy image of tissue being examined from ultrasoundsignals; acquire needle echo data for needle frames associated with theanatomy image that are obtained with transmit beam angles including afirst transmit beam angle and a second transmit beam angle with respectto a longitudinal axis of a transducer probe that receives theultrasound signals; determine, based on the needle echo data, segmentsin the needle frames obtained with the first transmit beam angle and thesecond transmit beam angle; assign scores to the segments in the needleframes, a first score of the scores assigned to a segment indicatingthat the segment represents an interventional instrument; identify atleast one segment of the segments that is assigned the first score; setthe first transmit beam angle as a priority angle when the at least onesegment that is assigned the first score is detected in the needleframes with the first transmit beam angle; acquire one or more firstframes of the needle frames with the first transmit beam angle that isset based on the priority angle determination at a first number ofreceive lines; and acquire one or more second frames of the needleframes with the second transmit angle at a second number of receivelines that is different from the first number.
 14. The ultrasoundimaging system of claim 13, wherein the one or more processors areconfigured to adjust a frame rate of one or more other frames of theneedle frames obtained with transmissions that are not in a beamsteering direction corresponding to the priority angle.
 15. Theultrasound imaging system of claim 13, wherein the one or moreprocessors are configured to adjust a line density of one or more otherframes of the needle frames obtained at transmission angles that are notin a beam steering direction corresponding to the priority angle. 16.The ultrasound imaging system of claim 13, wherein the receive lines arebeamformed in parallel for each transmit beam to produce the needleframes, and wherein the one or more processors are configured to adjusta number of the receive lines that are beamformed in parallel fromtransmission angles that are not in a beam steering directioncorresponding to the priority angle.
 17. The ultrasound imaging systemof claim 13, wherein the one or more processors are configured todecrease the first number of receive lines that are beamformed inparallel for each transmit beam to produce the one or more first framesobtained at the first transmit beam angle.
 18. The ultrasound imagingsystem of claim 13, wherein the one or more processors are configured toincrease the second number of receive lines that are beamformed inparallel for each transmit beam to produce the one or more second framesobtained at the second transmit beam angle.
 19. The ultrasound imagingsystem of claim 13, wherein the processor is configured to blend theneedle echo data from the segment with the tissue echo data for theanatomy image of tissue being examined.
 20. The ultrasound imagingsystem of claim 13, wherein the at least one segment of the segmentsthat is assigned the first score is to be blend with the tissue echodata.